CN102749640B - For the heat-staple pet detector of hybrid PET-MR system - Google Patents
For the heat-staple pet detector of hybrid PET-MR system Download PDFInfo
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- CN102749640B CN102749640B CN201210232331.9A CN201210232331A CN102749640B CN 102749640 B CN102749640 B CN 102749640B CN 201210232331 A CN201210232331 A CN 201210232331A CN 102749640 B CN102749640 B CN 102749640B
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- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/16—Measuring radiation intensity
- G01T1/1603—Measuring radiation intensity with a combination of at least two different types of detector
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- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
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- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/38—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field
- G01R33/3806—Open magnet assemblies for improved access to the sample, e.g. C-type or U-type magnets
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- G01R33/38—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field
- G01R33/385—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field using gradient magnetic field coils
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- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
- G01R33/48—NMR imaging systems
- G01R33/4808—Multimodal MR, e.g. MR combined with positron emission tomography [PET], MR combined with ultrasound or MR combined with computed tomography [CT]
- G01R33/481—MR combined with positron emission tomography [PET] or single photon emission computed tomography [SPECT]
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Abstract
In hybrid PET-MR system, in aperture (14), increase pet detector element (30) make it mutually close with gradient coil (16).Accommodating fluid cooling medium is to transmit the heat from pet detector element (30).Heat guard (80) makes fluid coolant and pet detector element (30) and gradient coil (16) adiabatic.In certain embodiments, first coolant path (90) and electron device thermal communication, second coolant path (92) and photo-detector thermal communication, and thermal boundary (94,96) be arranged between the first and second coolant path, make the first and second coolant path can be in different temperatures (T
e, T
d).In certain embodiments, the heat pipe (110) of sealing and heat sink thermal communication, make working fluid experience vaporization/condensation circulation in heat pipe with from detector element heat sink transferring heat.
Description
The divisional application that the application is the applying date is on June 23rd, 2008, application number is 200880023164.9, denomination of invention is the Chinese patent application of " the heat-staple pet detector for hybrid PET-MR system ".
The application relates to diagnosing image technical field.The present invention is particularly useful for mixing PET (positron emission tomography)-magnetic resonance (PET-MR) system, wherein the heater element of pet detector element and MR system leans on very near, and will specifically with reference to such hybrid PET-MR system come present invention is described.Because pet detector element self also produces heat, therefore the application is not limited to commingled system, but may be used for independently PET system, PET/CT(computerized axial tomography) system or the NMS except PET, such as single photon emission computerized axial tomography (SPECT) system.
In bore-type MRI system, the main magnet of large solenoid produces magnetic field along the axle in aperture.Usually, main magnet is the closer to imaging region, and the cost efficiency of design is higher.From main magnet, normally gradient coil, shim coil (inserting gradient coil assembly sometimes), radio frequency (RF) shield and RF coil inwards.These coils, or MR bore components occupies more spaces.Therefore, even if before in the aperture of Solid-state pet detector system being introduced MR system, space is also of great rarity.Pet detector must near MR bore components.Also vertical field open MR system can be utilized to build PET-MR system.Same space constraint is also applicable to this system.
Gradient coil especially can produce a large amount of heat.In MR scan period, the about 15kW of gradient coil mean consumption, peak level is higher.This may cause gradient coil temperature to raise, and can use water cooling by the temperature limiting of gradient coil to about 70 ° of C.RF coil also can generate heat.When by pulse action, RF coil and gradient coil also can produce stray magnetic field, the metal parts reciprocation that the stray magnetic field become time this may shield with the RF such as built into specific purpose of pet detector, and produce extra heat.
The pet detector element of oneself heating uses Air flow usually.Because photo-detector is to thermo-responsive (temperature often raises 10 ° of C, and dark noise just doubles), temperature limiting below working temperature photo-detector being cooled to gradient coil so close with it dark noise.But, because space is very valuable, therefore in PET-MR commingled system, cooling becomes a problem.The density of main magnet internal heating element is very high, and the space that can be used for cooling system is then minimum.
This application provides a kind of novel improved cooling system for the PET element in MR equipment aperture overcoming the problems referred to above and other problems.
According to an aspect, provide a kind of diagnostic imaging apparatus.Magnetic resonant part comprises main magnetic coil, gradient coil assembly and RF coil block.Main magnetic coil produces main field in the imaging region of this equipment.Gradient coil assembly superposes gradient magnetic on the main magnetic field.Shim coil can be positioned within gradient coil assembly and/or near.Shim coil superposition magnetic field for correcting, to improve the homogeneity of main field, comprises the main field disturbance in person under inspection's body.RF coil block is at least to transmitting RF signal in imaging region.PET (positron emission tomography) part comprises fluid-cooled detector array, and it is for detecting the radiation of instruction nuclear decay event.Detector array to be listed in temperature close to gradient coil assembly and the fluid cooling of the detector array cooled by convection cell and this detector array is maintained the lower temperature of the close gradient coil assembly of specific heat.At least one reconstruction processor produces image from the detectable signal coming from imaging region and represents.Display display is rebuild image and is represented.
According on the other hand, provide a kind of diagnosing image method.Main field is produced in imaging region.Superpose gradient fields on the main magnetic field.Extra shimming field can also be superposed.Magnetic resonance is brought out in person under inspection's body in imaging region.Detection magnetic resonance.In person under inspection's body, radiopharmaceutical is introduced when a certain generally before diagnosing image scanning.Detector array is utilized to detect the radiation of instruction Radioactive decay events.Utilize fluid coolant cooled detector array.The image that at least one in the magnetic resonance detected and radiation is reconstructed into person under inspection is represented.Display image represents.It is to be appreciated that these steps other order feasible equally and predicted these steps other order.
According to another aspect, disclose a kind of imaging system, it comprises: PET (positron emission tomography) part; Magnetic resonant part; Cooling system, at least one parts for cooling described PET (positron emission tomography) part and described magnetic resonant part shared by described cooling system.
According to another aspect, disclose a kind of radiation detector, it comprises: scintillator; Be arranged to detect in scintillator by with radiation reciprocation interested and the photo-detector of flicker that produces; Be configured to receive and process the electron device of electric signal of the instruction radiation interested received from photo-detector; The first coolant path of the coolant fluid of transport flow is configured to electron device thermal communication; The second coolant path of the coolant fluid of transport flow is configured to photo-detector thermal communication; And be arranged between the first and second coolant path and make the first and second coolant path can be in the thermal boundary of different temperatures.
According to another aspect, disclose a kind of imaging system, it comprises: first mode imaging system, and it defines aperture and is configured to gather first mode imaging data from inside, aperture; And PET (positron emission tomography) (PET) imaging system, it comprises the radiation detector array with the roughly ring-type according to paragraph immediately front of the aperture coaxial arrangement of first mode imaging system.
According to another aspect, disclose a kind of radiation detector, it comprises: scintillator; Be arranged to detect in scintillator by with radiation reciprocation interested and the photo-detector of flicker that produces; Be configured to receive and process the electron device of electric signal of the instruction radiation interested received from photo-detector; Heat sink; And the heat pipe of sealing with heat sink and photo-detector thermal communication.The heat pipe of sealing comprises working fluid and wick material or structure, configures this heat pipe and makes working fluid in heat pipe sealed, experience vaporization/condensation circulation with from photo-detector heat sink transferring heat.
According to another aspect, disclose a kind of imaging system, it comprises: MR scanner, and it defines aperture and is configured to the inner acquisition of magnetic resonance data from aperture; And PET (positron emission tomography) (PET) imaging system, it comprises the radiation detector array with the roughly ring-type according to paragraph immediately front of described aperture coaxial arrangement, to gather PET data from inside, aperture.
An advantage is that the cooling mechanism of pet detector element improves.
Another advantage is that the cooling mechanism of detector element is compact.
Another advantage is that gradient coil and pet detector element have independently cooling system.
Reading and understanding on the basis of instructions, those of ordinary skill in the art will be understood that other advantages of the present invention.
The present invention can be embodied in various parts and the layout of parts, and can be embodied in various steps and the arrangement of step.Accompanying drawing, only for illustrating preferred embodiment, should not be considered as limiting the present invention.
Fig. 1 is the schematic diagram of the combination PET/MR scanner according to the application;
Fig. 2 is the sectional view of the scanner aperture of Fig. 1, which particularly illustrates the detector array between gradient component and RF element;
Fig. 3 is the sectional view of the scanner aperture of Fig. 1, the detector array between each several part which particularly illustrating separate type gradient component;
Fig. 4 shows the schematic diagram of the coolant flow direction by parallel fluid channels;
Fig. 5 shows the schematic diagram of the detector cooling configuration providing difference to cool for electron device and photo-detector;
Fig. 6 shows the schematic diagram of the detector cooling configuration adopting heat pipe;
Fig. 7 shows the heat pipe array of detector cooling configuration of Fig. 6 and the schematic diagram of the planimetric map of the connection heat sink with fluid-cooled;
Fig. 8 shows and is similar to Fig. 6 but the schematic diagram comprising the detector cooling configuration towards heat sink thermal coupling at heat pipe two ends.
With reference to Fig. 1, depict the magnetic resonance (MR) of combination or mixing and the embodiment of PET data acquisition system (DAS) 10.This combination or commingled system 10 such as can gather both MR data and PET data from least part of crossover (as shown in the figure) or spatially adjacent MR and PET area of space.Should be understood that, multimodal systems carries out over time and space aliging for image or registration is desirable; Also forseeablely be by wide apart or be placed in spatially far different scanning device to take image, it is also feasible for adopting similar mode to take image.Illustrated scanner 10 is integrated system, but other scanners tendency seems feasible, such as side-by-side systems, plug-in type system etc. equally.Shown MR scanner comprises annular magnet 12, and described annular magnet comprises multiple conductor coils winding (with depicting with being with retiform block schematic in Fig. 1), and described coil winding produces static magnetic field B within imaging region 14
0.Magnet 12 can be superconducting property or electrical resistance property; In the previous case, magnet 12 is placed in cooled cryostat or other cooling system (not shown) usually.Illustrated magnet 12 is solenoid magnet, and it has the B of the relative level by imaging region 14
0.Although by B
0the polarity of field is shown for from right to left, but opposite polarity is also suitable.In other embodiments, magnet 12 can have C shape form or its orientation in order to produce other forms of the static magnetic field of vertical or other orientations.
MR scanner also comprises magnetic field gradient assembly, and in the exemplary embodiments of Fig. 1, magnetic field gradient assembly comprises gradient coil winding 16, and gradient coil winding 16, in response to the selectivity excitation to selected gradient coil winding 16, is worked in coordination with at static magnetic field B
0upper superposition magnetic field gradient.Optionally, magnetic field gradient coils, magnet or both can comprise unshowned other features for the formation of, stable and dynamic adjustments magnetic field, such as passive ferromagnetic shimming, active shimming coils etc.MR scanner also comprises radio-frequency (RF) excited and receiving system 18.This radio system comprises at least one and can carry out excitation with suitable radio frequency thus be placed in the parts of person under inspection's body underexcitation magnetic resonance of imaging region 14, such as illustrated whole body radio frequency coil 18.Coil 18 can also serve as the radio-frequency transmitter in order to the magnetic resonance received or send from imaging region 14 after detection RF excitation.In certain embodiments, different coil can be used for excitation and receive operation.Such as, internal coil 18 excite magnetic resonances can be used, can above the person under inspection in imaging region 14, with it or near the different local coil in location or special receiving coil (not shown) to detect magnetic resonance.Can predict and utilize internal coil, local coil or both various combinations to configure same MR scanner by different way.
The magnetic resonance samples received is stored in magnetic resonance samples storer 20.Magnetic resonance reconstruction processor 22 applies suitable reconstruction algorithm to rebuild magnetic resonance samples, and then forms reconstruction image, and is stored in magnetic resonance image memory 24 by reconstruction image.Reconstruction processor 22 applies the reconstruction algorithm matched with the selected space encoding adopted when producing MR data.Such as, Fourier transform reconstruction algorithm may be suitable for the MR data of rebuilding flute card coding.Optionally, before data store and complete reconstruction, (in-line) part for MR reconstruction can be carried out online.
Continue with reference to Fig. 1, illustrated combination or mixing MR and PET data acquisition system (DAS) 10 also comprise the radiation detector for carrying out PET data acquisition.In the illustrative examples of Fig. 1, the radiation detector 30 of annular array surrounds the aperture of commingled system.As mentioned below, illustrated array 30 comprises scintillator layers and one deck based on the photon detector of electron multiplier, but, can predict other detector configuration, such as, be arranged at the planar detector arrays near imaging region 14.Also predict solid-state radiation detector and solid state optical detectors.Radiation detector array 30 is configured to detect the gamma ray by the 511keV of positron-electron annihilation event emission.In PET data acquisition, suppose have two basic 511keV gamma ray detection events simultaneously to come from same positron-electron annihilation event, this positron-electron annihilation event is positioned at the somewhere of " line of response " (LOR) along the basic 511keV gamma ray detection events simultaneously of connection two.Sometimes also this bar response line is called projection or ray, the PET data of collection are called data for projection.
In conventional PET, basic 511keV gamma ray detection events is simultaneously defined as and occurs within selected short time window each other, such as, two 511keV gamma ray detection events within four nanoseconds.Any positron annihilation not occurring in field of view (FOV) center all will have the little time difference arriving opposing detector elements, and the traveling time that this time difference is proportional to gamma ray is poor, is approximately for four nanoseconds in the edge of FOV.Correlation technique, i.e. so-called time-in-flight pet or TOF-PET, utilize this little time difference, locates positron-electron annihilation event further with sub nanosecond precision along LOR.
The radiation detector array 30 of commingled system 10 is for gathering PET or TOF-PET data.Gamma ray detection events is processed by PET digital unit 32 and single-particle (singles) processing unit 34, wherein, PET digital unit 32 carries out the time to digital conversion (TDC) and analog to digital conversion (ADC) to detection event, and single-particle processing unit 34 carries out being polymerized, energy is estimated, time mark and location.Single-particle processing unit 34 optionally filters out the detection outside for the selection energy window of the 511keV gamma energy of expection.In certain embodiments, radiation detector is pixelation.In other embodiments, polymerization is applied to provide the further spatial localization refinement of the gamma ray detection events of definition projection by the block readout algorithm of such as Anger logic etc.Meet detection processor 36 and adopt time windowing to identify the gamma ray detection events substantially simultaneously occurring also therefore to correspond to common positron-electron annihilation event (and therefore definition projects or line of response).
For TOF process, use identify basic while or the detection event that meets between mistiming spatially estimate positron-electron annihilation event along line of response.
PET or the TOFPET data of gained are stored in PET data-carrier store 38.Should be understood that, PET data can be stored before or after coincidence determination.PET reconstruction processor 40 utilizes suitable reconstruction algorithm process projection or localized projection data to rebuild image to produce, and is stored in PET image storer 42 by reconstruction image.Such as, maximum likelihood expectation maximization (ML-EM), filter back-projection algorithm except ML-EM or iterative reconstruction algorithm can be adopted.The system of Fig. 1 comprises the continuous radiation detector array 30 for PET, and it encloses person under inspection completely.Around the imaging artefacts that not exclusively may cause because " disappearance " projection or line of response cause.Such as, some projection may be lost, thus the normal information about relevant position provided by this projection cannot be provided.Advantageously, if gather and rebuild time-of-flight PET data, even if so around in incomplete situation, the flight time, localization also provided the additional information compensating institute's loss of information.But, also have other compensate not exclusively around mode, certainly also predict other detector configuration in the application.
Optionally, carry out MR and PET acquisition simultaneously.Alternatively or cumulatively, can sequentially (such as MR is followed by PET before this, otherwise or) maybe can carry out MR and PET acquisition with interweaving.The MR of image registration processor 50 spatially registration reconstruction and PET image, and the MR of optionally registration reconstruction in time and PET image.If create out the image of common registration, just these images are stored in co-registration image memory 52.Display device 54 suitably shows the image of such registration, utilizes suitable two dimension or 3 D rendering software to draw, or otherwise process.
There is provided the first cooling system 56 this gradient coil is cooled to about 70 ° of C or lower when gradient coil 16 is operated in maximum average power level.Detector array 30 heat close to gradient coil 16, this is because gradient coil and detector array 30 fully close, be enough to make heat be transmitted to detector array 30 from gradient coil.There is provided the second cooling system 58 detector array 30 to be cooled to about 30 ° of C or lower, more wish to be cooled to about 20 ° of C, although it is hot close with gradient coil 16.
Referring now to Fig. 2, provide the enlarged drawing in imaging aperture.As previously mentioned, in one embodiment, detector array 30 extends 360 ° around the longitudinal axis in imaging aperture.Can say that for RF coil 18, gradient coil 16 and main magnet 12 are kindred circumstances.In the embodiment of fig. 2, detector array 30 is between gradient coil 16 and the RF shielding 60 for RF coil 18.In separate type gradient coil embodiment, as shown in Figure 3, detector array 30 can between each several part of gradient coil 16.Also predict other positions of detector array 30, such as, insert aperture as required and the removable system therefrom removed.
In in the embodiment shown in figs. 2 and 3 any one, detector array 30 and gradient coil 16 lean on very near.Active cooling makes detector array 30 keep not reaching thermal equilibrium with gradient coil 16.In order to make detector array 30 remain on acceptable working temperature, as shown in Figure 4, for detector array 30 provides closed circuit fluid cooling system 58.Fig. 4 is the cross-sectional, close up view of detector array 30.The electron device 66 that detector array 30 mainly comprises flash layer 62, optical detector elements 64 and is associated.Detector array 30 is all encapsulated within RF shielding case 68.Shielding case 68 prevents the driving pulse from RF coil 18 and the magnetic resonance signal from imaging region 14 from detector array 30, producing glitch.And, RF shielding prevent the irrelevant signal that produced by pet detector by MRRF coil transduces to.As previously mentioned, all bore components, comprise detector array 30, all extend 360 ° around aperture.
The room temperature when temperature range of gradient coil is never run or slightly cold until 70 ° of C of run duration.Aperture space similarly raised temperature around.In addition, the electron device 66 of pet detector can produce heat.The Stray field energy from pulse MR field be deposited in the RF shielding material of surrounding also produces extra heat.So, in order to prevent the operation of all these thermals source to detector array from having a negative impact, to pet detector array 30 applicating fluid cooling system 58.At least one surface of detector is allowed to cool.In one embodiment, fluid cooling is carried out to the surface near electron device and gradient coil, and make the end of detector adiabatic.In another embodiment, all fluid cooling is carried out to peripheral surface and end face.In yet another embodiment, as shown in Figure 4, fluid cooling is carried out to all palp sides of detector.Cooling fluid is guided by conduction pathway 70.Passage 70 by high heat conduction nonferrous material, such as copper, aluminium or stainless steel manufacture.Because detector array 30 itself is sealed, therefore also sealed by RF shielding material 68 from the passage 70 of the outside heat conduction of detector.Can shield outside 68 at RF and use different magnetic inert materials.Specifically, transfer passage 72 can be manufactured by thermal insulation material or encapsulate, and makes cooling fluid can not walk heat from the component tape of detector array 30 upstream, like that can to become efficiency in heat not high removing from detector array 30 itself.In one embodiment, transfer passage extends between RF screen 60 and gradient coil 16.
Cooling system is configured to pet detector 30 and provides high efficiency cooling, saves space simultaneously.For this purpose, cooling duct 70 is preferably welded or is otherwise directly thermally connected to the thin flat passage of Circuits System 66.Also preferably increase passage 70 and can not increase the volume of all assemblies, such as arrange passage 70 in complementary fashion, the circuit board faced by making can be combined together, and wastes the space between them hardly simultaneously.
The such mode of the closed conducting path of gradient fields can be coupled to avoid generation and configure cooling duct 70 around detector array 30.In one embodiment, this extends passage to realize in tortuous mode by the main axial direction along crossing over electron device bearer circuit system 66.When cooling side, cooling duct can extend radially.Annular channel is avoided to decrease the generation of vortex flow.For ingress path 72 and outlet pathway 74 manufacturing hole in RF shell 68.Waveguide can be utilized to realize this some holes.Can provide cooling circuit in Dielectric breaks 76 to block channel conductive paths.Heat exchanger unit 78 provides flowing and temperature to control to cooling fluid.Heat interchanger 78 can also make cooling fluid cool to lower than room temperature, more effectively to remove heat from detector array 30.Air flow can be carried out by heat exchanger 78 self within imaging chamber or adjacent room.Another selection is that heat interchanger 78 is connected with larger cooling system (total cooling systems of such as building) interface.Can by the transfer of heat from cooling medium to another fluid road and to be discharged to rooftop air conditioning compressor outer etc.
In one embodiment, cooling fluid has the hot transport characteristics of expectation and the minimum pure water of electric conductivity or deionized water.The flow velocity of cooling medium is proportional to total electronics power dissipation, is inversely proportional to outlet-inlet temperature difference.Flow path can comprise parallel pathways, to make the temperature rise of each circulative accumulation minimum and to realize overall pressure drop.Single path may hold lower volume and fluid ability, and pressure drop increases, but the part of detector array 30 in flow path end and the part in flow path beginning may can not get cooling, this means that further downstream detector parts possibly cannot be cooled to the temperature identical with upstream components.This may mainly cause uneven image artifacts.Local provisions, such as heat sink, can provide and leave from electron device 66 thermally conductive pathways arriving fluid passage 70.Or, can by other coolant fluids, such as refrigerant, liquid nitrogen, forced draft etc. are used as the fluid coolant in passage 70, and should be understood that, " fluid " that use in the application comprises all these.When using the cooling medium colder than room temperature, air stream can be provided to prevent condensation with auxiliary by aperture.
In another embodiment, heat conduction dielectric oil can be used as cooling medium.In this embodiment, dielectric coolant directly can contact with detector element with electron device 66, instead of by conduit wall indirect contact.In this submergence cooling embodiment, whole detector array 30 is all encapsulated in the sealing chamber of Fluid Sealing, such as, in the involucrum of cylindricality or cartouche.This method can save a lot of fluid passage and heat sink.The possibility that gear pulls to reduce uneven flow velocity and focus can be comprised in sealing chamber.
In another embodiment, the cooling of amber ear note is used to carry out cooled detector array 30.Can by this be used as independent solution, selectivity amber ear note maybe can be used to cool, as one or more additive methods above-mentioned supplementary come cooling failure point.In the separate type gradient coil configuration of Fig. 3, advantageously, arrange that refrigeratory 56 and the gradient cooling circuit that is associated are with from inside to outside, namely carry out cooling separation type gradient coil from the region in the gap closing on separate type gradient coil to the outer extremities of separate type gradient coil.This is favourable, because gradient coil will be the coldest, has the most stable temperature at the near gaps of proximity detector array 30.Optionally, cool circuit also to concentrate near gaps, to improve the gradient coil cooling effectiveness near detector array 30 further.
In another embodiment, common fluid cooling system is used to cool both gradient coil 16 and detector array 30.An advantage of this embodiment is not only cost-saving but also save space.But shortcoming is that the temperature of detector array 30 can be subject to the impact of gradient coil 16 temperature.Detector array can be cooled to lower temperature by cooling fluid, and cooling fluid leaves detector array and goes cooling or help cooling gradient coil 16.Also can utilize discrete circuit, make only have a part for heat interchanger 78 to be shared.In two cooling system environment, heat guard 80 can be used to be opened with detector array 30 is heat insulation by gradient coil 16 at least in part.In this way, independent benchmark can be set for each cooling system.Utilize combination cooling system, gradient coil 16 can be cooled to the expectation working temperature of detector array 30, because the thermal mass of gradient coil 16 is larger, this will expend much bigger accurate cooling.Another option allows combination cooling system need the element of cooling to have independently heat interchanger for pet detector array and other.
With reference to Fig. 5, show the detector cooling configuration for electron device 66 and photo-detector 64 provide difference to cool.Electron device such as can comprise the time to digital quantizer (TDC) element, analog to digital converter (ADC) element, field programmable gate array (FPGA) or other logic elements, low leakage (LDO) voltage stabilizer etc.These parts produce in a large number wants removed heat, as long as but electron device 66 maintain and show in Figure 5 for T
esuitable low working temperature, the general and temperature of the performance of electron device 66 does not have strong correlation.So close and the first cooling path 90 of cooling electronic device 66 shows for F for providing in Fig. 5
ehigh coolant rate of flow of fluid, to realize high heat trnasfer.
Such as the photo-detector 64 of silicon photomultiplier cell (SiPM) element or photomultiplier has the operating characteristic being strongly depend on temperature.Such as, for some SiPM detectors, temperature often raises 1 ° of C, and gain increases about 5-10%.But photo-detector 64 generally exports a lot of heat fewer than electron device 66.So, near and the second cooling path 92 cooling photo-detector 64 show for F for providing in Fig. 5
dcomparatively low discharge, photo-detector 66 is maintained substantially time-independent accurate temperature T by described second cooling path
d.
Arranging electronic device 66 and the cooling path 90 associated, arrange photo-detector 64 and the cooling path 92 associated on the other hand, make it substantially heat insulation each other on the one hand.This can by being arranged between electron device 66 and the cooling path 90 associated on the one hand, and be arranged at the passive thermal insulation material 94 between photo-detector 64 and the cooling path 92 associated on the other hand, such as adiabatic dielectric material or clearance realize.Additionally or alternatively, this can be realized by the active thermal provided by isolation cooling path 96, has with flow F in isolation cooling path 96
ithe coolant fluid of flowing.
Scintillator 62 does not generally need cooling.But scintillator 62 is positioned to very near photo-detector 64, and photo-detector necessarily remains on equilibrium temperature.Therefore, in the 5 embodiment of figure 5, additional passive thermal insulation material 98 is set around scintillator 62, makes passive heat guard 94,98 roughly comprise the equilibrium temperature region comprising photo-detector 64.Detector temperature management system is suitably contained in as a whole around in the external container 100 of detector module, and its side has coolant fluid stream F
e, F
d, F
ibe assigned to the coolant fluid entrance 102 in cooling path 90,92,96, and have in relative side from detector module discharge coolant fluid stream F
e, F
d, F
icoolant fluid outlet 104.Corresponding coolant fluid stream F is suitably defined by the flow resistance of cooling path 90,92,96 (or equivalently, fluid conductance)
e, F
d, F
idifferent relative velocities.Optionally, one or more temperature sensor 106 is set to measure the temperature of photo-detector 64, control flow into entrance 102(or, flow out outlet 104), temperature sensor 106 to be maintained the temperature reading of expectation.Or, temperature sensor can be arranged to the temperature T in the coolant fluid path 92 measuring cooling photo-detector 64
d, because this temperature T
dshould close to the temperature of photo-detector 64.Based on detector temperature (or generally based on temperature T
d) controlled cooling model agent fluid stream is favourable, because this to maintain stable key temperatures.
Although not shown, it is also envisioned that and provide active valve to control, such as can from external control or the Valve controlling of temperature feedback control, regulate the relative velocity F entering cooling path 90,92,96
e, F
d, F
i.In addition, although not shown, can predict and provide around the passive thermal insulation material of electron device 66 with the flow path 90 associated.
In another modification forseeable, adverse current is utilized to arrange to reduce the thermograde within module for each single plane, thus the cooling of the module of amendment shown in Fig. 5.This can be realized by the same side that entrance 102 and outlet 104 are placed on detector module.Estimate to use adverse current to arrange and thermal gradient will be reduced 1-2 the order of magnitude, can estimate that this can improve temperature stability.Or, cooling can be cascaded up, because estimate that the heat that the heat produced by photo-detector 64 reality produces than electron device 66 is low 100 times.Adverse current or cascaded design any one in, advantageously first cool photo-detector 64 then cooling electronic device 66, such as, first make cooling medium flow through cooling path 92 near photo-detector 64, then flow through the cooling path 90 near electron device 66.This of coolant fluid stream arranges the temperature T promoted near photo-detector 64
dwith the temperature T near electron device 66
ecompare more accurately and lower.The temperature T of electron device 66
ebe the dissipation due to most of heat, but the temperature of electron device is not necessarily accurate, it can be cooled by the coolant fluid after flowing through near photo-detector 64.
As another modification of Fig. 5 design, with reference to the illustration II shown in figure 5, micro-Peltier elements 108 can provide initiatively controlled thermal resistance between cooling path 92 and photo-detector 64.Such as, the Peltier's element of standard is suitably based on bismuth telluride (Bi
2te
3) and bismuth selenide (Bi
2se
3).Can use and be similar to for utilizing the Peltier's element based on silicon to cool the layout of semiconductor (such as described in the U.S. Patent No. 6800933 of the people such as Mathews, this patent documentation is incorporated herein by reference), wherein miniature amber ear note device is arranged in the immunity region of semiconductor-on-insulator (SOI) substrate top used in photo-detector 64.Also these structures are realized in the autonomous device can installed at photo-detector 64 back.In this fashion, can tuning localized temperature gradients being controlled within about 0.1 ° of C or less, to guarantee that each optical detector elements has the temperature of precise constant.In these embodiments, the temperature of heat eliminating medium is necessarily equally not low with the temperature of photo-detector, thus eliminates condensation and without the need to high costs by below medium cool to room temperature.
The radiation detector system of FIGURE of Fig. 5 have employed coolant fluid.Coolant fluid can be such as deionized water, forced draft, refrigerant etc.In such an embodiment, such as, utilize the permanent connection that is such as welded to connect or such as screw thread couple or the dismountable connector that disconnects fast by entrance 102 and export 104 and suitably to supply with outside and return line (circuit 72,74 of such as Fig. 4) is connected.
With reference to Fig. 6 and 7, in another embodiment, use one or more heat pipe, the heat pipe 110 of such as illustrated array of parallel linear, provide from each parts of radiation detector module to one or more by the Heat Conduction Materials such as such as thermal conductive ceramic, aluminium oxide, aluminium nitride make heat sink 112 heat trnasfer.Can also be heat sink 112 heat-conducting metals using such as copper, but by its lamination or otherwise should configure, to suppress the formation of vortex flow.Optionally, cooling fluid pathway 114, by heat sink 112, is transferred to heat in heat sink 112 to remove heat pipe 110.
Each heat pipe 110 comprises the internal volume 120 of sealing, and this internal volume comprises at least one working fluid, such as water, solvent etc. as alcohol, or comprises the potpourri of working fluid.The inside surface of internal volume 120 arranges wick material or structure 122 or another kind ofly supports capillarity or capillary material or structure, wick material or structure are made up of the porous material being formed with groove on the surface.
At work, working fluid near heat pipe 110 away from heat sink 112 end 124 place or evaporate at other " focus " places along heat pipe 110.Transmit heat of vaporization from focus to the working fluid of evaporation, diagrammatically illustrate this point with arrow 126.Due to vapor concentration gradients, working fluid 126 heat sink 112 of evaporation moves.The working fluid 126 of evaporation is in the end 128 place condensation closing on heat sink 112 near heat pipe 110.Working fluid condenses from condensing working fluid heat sink 112 at near-end 128 and displaced the heat of condensation.The working fluid condensed is inhaled to the far-end of heat pipe 110 to pumpback by the capillarity that is associated with wick material or structure 122 or capillary action.When working fluid evaporates at focus again, complete heat transfer cycle.Advantageously, the coagulating liq backflow that the capillary force in wick material or structure 122 causes has nothing to do with the locus of heat pipe 110.
In order to be used in comprise MR parts commingled system in, heat pipe 110 is preferably made up of non magnetic and electrically non-conductive material, such as Thermal Conductivity Ceramics Used, such as aluminium nitride or aluminium oxide.If use metal or other conductive materials, then they should be carried out lamination, thus be arranged to compound substance in non-conductive host material, or otherwise be configured to the formation suppressing vortex flow.As shown in Figures 6 and 7, the heat pipe 110 of this array is roughly smooth, and is arranged between photo-detector 64 and the electron device 66 be associated, to cool both.Because the working fluid 126 of evaporation is transported rapidly, therefore between hotter electron device 66 and colder photo-detector 64, there is intrinsic temperature isolation.
Advantageously, connection between heat pipe 110 and heat sink 112 can contact 130 realizations by heat-transfer surface, optionally strengthened by pressure fitted, be threaded etc., need not cooling fluid be had to flow between heat sink 112 and heat pipe 110, therefore do not comprise fluid therebetween and connect.Advantageously, heat pipe 110 is permanent seal unit, does not open heat pipe 110 when installing or removing radiation detector module.
Another advantage is, the temperature of heat pipe 110 outside be substantially subject to working fluid evaporating temperature control and along heat pipe 110 substantially constant.Evaporating temperature is the function of one or more heat eliminating mediums.
With reference to Fig. 8, in order to reduce thermal gradient further, should predict and make each heat pipe 110 carry out thermal communication with more than one heat sink 112, such as, all having heat sink 112 at the two ends of heat pipe 110 as shown in Figure 8.Also should predict the heat pipe arranging crossed linear array, or use the heat pipe of general planar, or adopt other heat pipe geometric configuratioies to remove and temperature stability to strengthen heat.
The embodiment of Fig. 8 also comprises the photo-detector 64 and electron device 66 that are integrated into individual layer, such as, in the single common layer being monolithically integrated in silicon substrate material or in.For example, see WO2006/111883A2(2006 is open for October 26, this patent documentation is incorporated herein by reference), it relates to a kind of digital silicon photomultiplier for time-in-flight pet (SiPM), wherein digital SiPM comprise single chip mode to be formed in common silicon substrate or on detector array layer and immersion (buried) cmos digital treatment circuit layer.In the embodiment in fig. 8, heat pipe 110 is all provided with wick material or structure 122 at internal volume 120 away from on the inside surface at cooled element 64,66 place.But due in the embodiment in fig. 8, cooled element 64,66 is arranged at heat pipe 110 side together, therefore can predict and only arrange this wick material or structure on the inside surface near cooled element 64,66.
As another kind of modification, although in the embodiment shown in Fig. 6-8, heat pipe 110 directly contacts with cooled element 64,66 or leans on very near, in other embodiments, heat pipe can be arranged in one block of thermal conductive ceramic material or non-conductive synthetic material, this material again with the close thermo-contact of cooled element 64,66.
Although be described in the illustrative context of hybrid imaging system being associated with magnetic resonance imaging, but should understand, it is also envisioned that and to be used in other imaging systems adopting radiation detector with reference to radiation detector module cooling configuration disclosed in Fig. 4-8, such as, be used in independently PET imaging system, PET/CT(computerized axial tomography) in imaging system, gamma camera etc.
Describe the present invention with reference to preferred embodiment.Reading and understanding on the basis of instructions, other people can expect various modifications and changes.As long as all such modifications and change belong in the scope of claims or its situation of equal value, so the invention is intended to be understood to include all this modifications and changes.
Claims (5)
1. a radiation detector, comprising:
Scintillator (62);
Be arranged to detect in described scintillator by with radiation reciprocation interested and the photo-detector (64) of flicker that produces;
Be configured to receive and process the electron device (66) of the electric signal of the instruction received from described photo-detector radiation interested;
First coolant path (90) of the coolant fluid of transport flow is configured to described electron device thermal communication;
Second coolant path (92) of the coolant fluid of transport flow is configured to described photo-detector thermal communication; And
Being arranged between described first coolant path (90) and described second coolant path (92) makes described first and second coolant path can be in different temperatures (T
e, T
d) thermal boundary (94,96).
2. radiation detector according to claim 1, wherein, described thermal boundary comprises at least one that (i) passive thermal insulation material (94) and (ii) stream have in the isolation cooling path (96) of coolant fluid.
3. radiation detector according to claim 1, wherein, described second coolant path (92) is maintained at basicly stable lower temperature (T
d), and described first coolant path (90) is maintained at comparative high temperature (T
e).
4. radiation detector according to claim 1, also comprises:
Be arranged at the micro-Peltier elements (108) between described second coolant path (92) and described photo-detector (64).
5. an imaging system, comprising:
First mode imaging system (10), it defines aperture (14) and is configured to gather first mode imaging data from inside, described aperture; And
PET (positron emission tomography) (PET) imaging system, it comprises the array with the roughly ring-type of the radiation detector according to claim 1 of the described aperture coaxial arrangement of described first mode imaging system.
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| US60/947,483 | 2007-07-02 | ||
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| US61/027,043 | 2008-02-08 | ||
| CN2008800231649A CN101688916B (en) | 2007-07-02 | 2008-06-23 | Thermally stabilized pet detector for hybrid PET-MR system |
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| Application Number | Title | Priority Date | Filing Date |
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| CN2008800231649A Division CN101688916B (en) | 2007-07-02 | 2008-06-23 | Thermally stabilized pet detector for hybrid PET-MR system |
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| CN201210232331.9A Active CN102749640B (en) | 2007-07-02 | 2008-06-23 | For the heat-staple pet detector of hybrid PET-MR system |
| CN201410538371.5A Active CN104316953B (en) | 2007-07-02 | 2008-06-23 | Heat-staple pet detector for hybrid PET-MR systems |
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| EP (1) | EP2176683B1 (en) |
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| CN101688916B (en) | 2013-05-01 |
| CN104316953A (en) | 2015-01-28 |
| US20100188082A1 (en) | 2010-07-29 |
| EP2176683B1 (en) | 2017-08-09 |
| US8378677B2 (en) | 2013-02-19 |
| CN101688916A (en) | 2010-03-31 |
| CN104316953B (en) | 2018-05-15 |
| WO2009004521A2 (en) | 2009-01-08 |
| EP2176683A2 (en) | 2010-04-21 |
| WO2009004521A3 (en) | 2009-10-15 |
| CN102749640A (en) | 2012-10-24 |
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